WO2011120340A1 - 一种超声换能器 - Google Patents

一种超声换能器 Download PDF

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Publication number
WO2011120340A1
WO2011120340A1 PCT/CN2011/000575 CN2011000575W WO2011120340A1 WO 2011120340 A1 WO2011120340 A1 WO 2011120340A1 CN 2011000575 W CN2011000575 W CN 2011000575W WO 2011120340 A1 WO2011120340 A1 WO 2011120340A1
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WO
WIPO (PCT)
Prior art keywords
spherical
cavity
ultrasonic
ultrasonic transducer
center
Prior art date
Application number
PCT/CN2011/000575
Other languages
English (en)
French (fr)
Inventor
王智彪
王�华
曾德平
Original Assignee
重庆融海超声医学工程研究中心有限公司
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by 重庆融海超声医学工程研究中心有限公司 filed Critical 重庆融海超声医学工程研究中心有限公司
Priority to CA2786197A priority Critical patent/CA2786197C/en
Priority to JP2012550306A priority patent/JP5657701B2/ja
Priority to ES11761915.5T priority patent/ES2556779T3/es
Priority to EP11761915.5A priority patent/EP2524651B1/en
Priority to KR1020127018185A priority patent/KR101378207B1/ko
Priority to RU2012126858/14A priority patent/RU2523152C2/ru
Priority to US13/520,699 priority patent/US9242121B2/en
Publication of WO2011120340A1 publication Critical patent/WO2011120340A1/zh

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N7/02—Localised ultrasound hyperthermia
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B06—GENERATING OR TRANSMITTING MECHANICAL VIBRATIONS IN GENERAL
    • B06B—METHODS OR APPARATUS FOR GENERATING OR TRANSMITTING MECHANICAL VIBRATIONS OF INFRASONIC, SONIC, OR ULTRASONIC FREQUENCY, e.g. FOR PERFORMING MECHANICAL WORK IN GENERAL
    • B06B1/00—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency
    • B06B1/02—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy
    • B06B1/06—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy operating with piezoelectric effect or with electrostriction
    • B06B1/0607—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy operating with piezoelectric effect or with electrostriction using multiple elements
    • B06B1/0622—Methods or apparatus for generating mechanical vibrations of infrasonic, sonic, or ultrasonic frequency making use of electrical energy operating with piezoelectric effect or with electrostriction using multiple elements on one surface
    • B06B1/0637—Spherical array
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N29/00—Investigating or analysing materials by the use of ultrasonic, sonic or infrasonic waves; Visualisation of the interior of objects by transmitting ultrasonic or sonic waves through the object
    • G01N29/22—Details, e.g. general constructional or apparatus details
    • G01N29/24—Probes
    • G—PHYSICS
    • G10—MUSICAL INSTRUMENTS; ACOUSTICS
    • G10K—SOUND-PRODUCING DEVICES; METHODS OR DEVICES FOR PROTECTING AGAINST, OR FOR DAMPING, NOISE OR OTHER ACOUSTIC WAVES IN GENERAL; ACOUSTICS NOT OTHERWISE PROVIDED FOR
    • G10K11/00—Methods or devices for transmitting, conducting or directing sound in general; Methods or devices for protecting against, or for damping, noise or other acoustic waves in general
    • G10K11/18—Methods or devices for transmitting, conducting or directing sound
    • G10K11/26—Sound-focusing or directing, e.g. scanning
    • G10K11/32—Sound-focusing or directing, e.g. scanning characterised by the shape of the source
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/44—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device
    • A61B8/4444—Constructional features of the ultrasonic, sonic or infrasonic diagnostic device related to the probe
    • A61B8/4455—Features of the external shape of the probe, e.g. ergonomic aspects
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0056—Beam shaping elements
    • A61N2007/006—Lenses
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0056—Beam shaping elements
    • A61N2007/0069—Reflectors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0078—Ultrasound therapy with multiple treatment transducers

Definitions

  • the invention belongs to the technical field of ultrasonic therapy, and in particular relates to an ultrasonic transducer. Background technique
  • the manner in which the above technical problems are solved in the prior art is generally achieved by designing an ultrasonic transducer.
  • the size and intensity of the ultrasonic energy focusing area are related to the emission area and frequency of the ultrasonic transducer.
  • the larger the emission area the larger the ultrasonic energy concentrated in the focusing area, and the ultrasonic energy is converted.
  • the higher the operating frequency of the device the shorter the wavelength of the transmitted ultrasonic wave, and the smaller the focus area, the higher the ultrasonic intensity.
  • an ultrasonic transducer In order to increase the emission area of the ultrasonic transducer, an ultrasonic transducer is disclosed in US 2006/0058678 A1, which fixes the ultrasonic source to an annular support to increase the emission area of the ultrasonic wave.
  • the design adopts a technical solution: the opposite toroids of each ultrasonic source are notched, and the ultrasonic transducer is compared with a transducer using a single ultrasonic source. The focus gain of the transducer is increased.
  • the ultrasonic transducer is provided with a gap on the opposite annular surface of the ultrasonic source, the effective emission area of the ultrasonic wave source on the ring surface is reduced, and the gap causes loss of ultrasonic energy, which reduces the treatment head as a ring.
  • the overall focus area energy is detrimental to increasing the focusing power of the ultrasonic transducer.
  • the technical solution simply increases the emission area of the ultrasonic transducer so that the energy is superimposed at the focus. At a lower frequency, due to the longer wavelength, the focusing ability of the ultrasonic wave is not good, and the focusing area is better.
  • the intensity of the ultrasound in the focal region is weak, and the coagulation necrosis of the target region cannot be formed quickly and effectively during the ultrasound treatment; and if the operation is performed at a higher frequency, the penetration of the ultrasound in the tissue Poor sex, in the ultrasound treatment of deep tissues of the human body, the ultrasound needs to pass through the human skin, bone tissue, gas-containing tissue, nerve tissue and other tissues to reach the focus position, and the above-mentioned tissue has absorption, reflection, etc. for the transmitted ultrasonic waves. Function, which not only causes the energy reduction and dispersion of the focal region, but also causes the temperature of these tissues to rise after the tissue absorbs the ultrasonic wave.
  • the transmitting power of the ultrasonic transducer When the transmitting power of the ultrasonic transducer is large, due to the Increased temperature may cause accidental damage to the tissue.
  • human tissue has a large nonlinear effect on ultrasonic waves, high-intensity ultrasonic waves are transmitted in human tissues, and a large part of ultrasonic waves are converted into higher harmonics of ultrasonic waves, which are absorbed by tissues.
  • Increasing the ultrasonic emission power of the transducer will produce a greater nonlinear effect, such that the increased ultrasonic energy cannot be efficiently transmitted to the desired focal region, creating an acoustic saturation phenomenon that affects the focus of the ultrasound.
  • the emission and reflection on the opposite side of the source of the ultrasonic transducer can be used to enhance the focus gain, as disclosed in the Chinese patent (Publication No. CN 101140354A) filed by the present applicant.
  • the resonant ultrasonic transducer uses a relatively arranged ultrasonic transducer and an ultrasonic reflecting unit to form a resonant cavity. Since the ultrasonic reflecting unit is equivalent to an ultrasonic transducer, the resonant cavity is actually equivalent to two symmetry.
  • the ultrasonic transducer is disposed, and the resonance of the ultrasonic wave in the cavity is such that the length of the focused area of the ultrasonic wave in the direction of the sound axis becomes shorter than when only a single ultrasonic transducer is used (two ultrasonic waves of the same frequency are opposite) They will interfere in the area where they meet, and they will be in phase at the center point when they interfere, and they will be non-in phase at other points, so the superposition of the two will result in weak off-center distribution, resulting in shortened ultrasonic focal length), which will make energy more concentrated. , the focus gain is greatly improved. With the operating mode of the resonator transducer, the gain of the transducer focus area can be made larger without increasing the emission area of the ultrasonic transducer.
  • the resonant cavity formed by the two transducers is not a circular closed spherical surface, and cannot form an effective acoustic resonance, and still some of the energy will be relatively set.
  • the opening portion in the middle of the two transducers escapes, and the ultrasonic energy emitted by the transducer cannot be fully utilized.
  • the required resonant cavity cannot produce sufficient gain in the focal region, or cause other focal regions to form and damage other normal tissues.
  • the length of the focal region is only compressed in the direction of the acoustic axis of the resonant cavity.
  • the length of the focal region in the other direction of the acoustic axis of the resonant cavity is not compressed, that is, formed Only the length of the focal region in the direction of the ultrasonic sound axis is compressed, and the volume of the focal region is not sufficiently reduced.
  • the size of the focus region of the ultrasonic transducer is still affected by the frequency, and the working condition at low frequencies cannot be achieved. Lower ultrasound also has good tissue penetration, thereby solving the technical problem of severe energy loss in the transmission path;
  • Fifth, the emission area of the ultrasonic transducer is not large enough. Summary of the invention
  • the technical problem to be solved by the present invention is to provide an ultrasonic transducer having a large ultrasonic emission area and an ultrasonic focusing ability which is hardly affected by the operating frequency of the ultrasonic transmitting source, in view of the above-mentioned deficiencies of the prior art.
  • the ultrasonic transducer includes one or more ultrasonic transmitting units, and the wavefront of the ultrasonic waves emitted by the one or more ultrasonic transmitting units is a spherical surface having the same radius, the one Or the plurality of ultrasonic transmitting units simultaneously have the function of reflecting ultrasonic waves, the one ultrasonic emitting unit forming a spherical resonant cavity/or the plurality of ultrasonic transmitting units together forming a spherical resonant cavity, and the inner cavity of the spherical resonant cavity
  • the shape is a spherical shell shape or a truncated spherical shell shape including a spherical core, and a focal region of the ultrasonic wave emitted by the one or more ultrasonic transmitting units is a spherical center of the spherical resonant cavity.
  • the inner cavity of the spherical cavity formed by the ultrasonic transmitting unit has a spherical shell shape or a spherical shell shape including a spherical core, and the cavity surface of the entire spherical resonant cavity is both ultrasonic emission.
  • the surface is again a reflecting surface of the ultrasonic wave, thereby increasing the effective ultrasonic emission area and increasing the number of reflections.
  • the two ultrasonic waves form a resonance inside the spherical resonant cavity, and Since the time at which the two ultrasonic waves reach the center of the sphere is the same, a plurality of resonance points are generated in the cavity of the entire spherical cavity, and the medium in the spherical cavity absorbs little ultrasonic waves (usually when the frequency of the ultrasonic wave is low, the medium pair
  • the ultrasonic wave absorption unit has a small reflection ultrasonic performance
  • the ultrasonic wave emitted from the ultrasonic wave emitting unit can be reflected multiple times in the spherical cavity, so that the ultrasonic wave is repeatedly in the spherical cavity.
  • the ultrasonic wave emitted from the surface of the spherical cavity and the ultrasonic wave reflected on the opposite surface form a resonance-enhanced focusing area at the center of the ball, thereby increasing the ball.
  • the ultrasonic intensity at the heart greatly improves the utilization of ultrasonic waves.
  • the core is further strengthened by multiple resonances, and the energy is multiplied, thereby further strengthening the ball.
  • the resonance of the heart position further increases the energy of the focus area.
  • the ultrasonic energy at the non-spherical position in the spherical cavity is relatively low relative to the ultrasonic energy at the center of the sphere because the number of resonance enhancements is rather limited. of,
  • the existing conventional ultrasonic transducer is used for direct focus treatment of the human body, the sound pressure at the focus is P, and the sound intensity is I;
  • the ultrasonic transducer of the present invention is used to treat the human body, and the ultrasonic emission unit is provided.
  • the frequency of the transmitted ultrasonic wave is the same as that used when the conventional ultrasonic transducer is used for treatment.
  • the ultrasonic transducer of the present invention attenuates the ultrasonic wave by about 10%, then after one reflection, the ultrasonic sound pressure is attenuated to The original 0. 9 times or so, that is, the sound pressure attenuation is 0. 9P, after two attenuations, the attenuation is about 0.81 times (assuming that only two reflections are performed, of course, the actual number of reflections is far more than twice).
  • the sound pressure attenuation 0. 81P
  • the ultrasonic emission and reflection processes are performed twice (ultrasonic emission unit) At the same time, it has the function of ultrasonic emission and ultrasonic reflection), so the total sound pressure at the center of the ball is 2 X 2. 71P
  • the ultrasonic transducer of the present invention achieves energy equivalent to nearly 30 times that of the conventional ultrasonic transducer. In the actual application process, as the number of reflections increases, the amount of attenuation is further reduced, and the focusing energy is higher. It can be seen from this that the ultrasonic energy at the focus of the ultrasonic transducer of the present invention is much higher than that of the existing ultrasonic transducer.
  • the spherical cavity formed by the ultrasonic transducer of the present invention may be in the shape of a spherical shell or a shape of a spherical shell including a spherical core.
  • shape of the inner cavity of the spherical cavity is a spherical shell shape, it is a spherical cavity in which the sound path is completely closed (or may also be referred to as "sound path sealing"), and the ultrasonic wave propagates only in the cavity. It does not diverge outside the cavity of the resonant cavity.
  • the so-called spherical center means that the shape of the inner cavity formed by the spherical cavity is perpendicular to the central axis thereof.
  • the acoustic path is closed, that is, the curve forming the inner cavity includes a circumferential curve of the passing center, thereby ensuring that the spherical resonant cavity forms an acoustic path in a circumferential direction perpendicular to its central axis. Closed (or also referred to as "sound path sealing", that is, a sound field distribution pattern in which no sound wave leaks in the circumferential direction, so that the circumferential direction is not issued
  • the ultrasonic transducer of the present invention can prevent all or most of the ultrasonic energy from escaping from the resonant cavity with respect to the conventional ultrasonic transducer (such as the Chinese patent disclosed in Japanese Patent No. CN 101140354A).
  • the conventional focused ultrasonic transducer causes the ultrasonic energy focusing area to be dispersed due to the edge effect of the ultrasonic emitting surface, and As the operating frequency of the ultrasonic transducer decreases, the edge effect The effect will become larger, resulting in a weakening of the ultrasound focusing ability (ie, the focal area will increase), so when performing ultrasound treatment, it is necessary to form coagulative necrosis at the treatment site, and the working frequency required for a general ultrasonic transducer is compared.
  • the current frequency range is 0.8 ⁇ Z-1 (MHZ.)
  • the acoustic path is sealed due to its one or more directions of ultrasonic propagation. Therefore, there is no diffraction phenomenon in the circumferential direction of the focus area, and there is no such phenomenon that the ultrasonic focusing ability is reduced as the ultrasonic frequency is reduced, which makes the focal length of the present invention almost free from ultrasound.
  • the transducer's transmission frequency (of course, for the spherical cavity of the spherical cavity, which is a spherical shell-shaped ultrasonic transducer including a spherical core, it only ensures that the ultrasonic focusing region passes through the center of the sphere and Compression is performed in a circle perpendicular to the axis of the sound, that is, only the focal region is compressed in all directions of the sound propagation plane, and therefore in the direction along its central axis
  • the lower limit range of the operating frequency of the ultrasonic transmitting unit in the present invention can be appropriately selected as compared with the ultrasonic transmitting unit in the existing ultrasonic transducer, and the operating frequency range is 20MHz ⁇ 10MHz, The preferred operating frequency range is 0. 1MHz - 0. 8MHz.
  • the ultrasonic transducer of the present invention can work effectively even in the case of low frequencies, such as a frequency of only 20 kHz.
  • the traditional ultrasonic transducer is impossible to generate a high sound field at such a low frequency.
  • the ultrasonic transducer unit in the ultrasonic transducer of the present invention is also an ultrasonic reflection unit.
  • the ultrasonic emission unit has the function of reflecting ultrasound at the same time), its focusing ability is strong, so it can work under low frequency conditions, and reduce the operating frequency of the ultrasonic transmitting unit, and it is also beneficial to increase the number of ultrasonic reflections (because the lower the frequency, the tissue The smaller the absorption of the ultrasound, the more the reflection occurs, so that the ultrasonic intensity at the focal region (spherical center) can be further increased.
  • the spherical resonant cavity of the present invention it is necessary to ensure that the spherical resonant cavity formed by the ultrasonic transmitting unit that emits the spherical wave satisfies the ultrasonic resonance superposition principle, that is, the diameter of the spherical resonant cavity is an integral multiple of the half wavelength of the emitted ultrasonic wave.
  • the ball-shaped inner cavity including the spherical core may be a ball-shaped spherical shell
  • the upper bottom surface S1 of the truncated spherical inner cavity is parallel to the lower bottom surface S2, and the distance from the upper bottom surface to the center of the sphere is not equal to the distance from the lower bottom surface to the center of the sphere.
  • the upper bottom surface S1 of the truncated spherical inner cavity is parallel to the lower bottom surface S2, and the distance from the upper bottom surface to the center of the sphere is equal to the distance from the lower bottom surface to the center of the sphere, and the shape can be maintained at the center of the sphere.
  • the aggregation gain is as large as possible.
  • the shape of the inner cavity of the spherical cavity It is also possible to adopt an irregularly shaped spherical table to cut the spherical shell shape.
  • the upper bottom surface and the lower bottom surface of the spherical trapping shell inner cavity including the spherical core are not parallel, and the distance from the upper bottom surface to the center of the sphere and the lower bottom surface The distance to the center of the ball may be equal or unequal.
  • the inner cavity of the spherical cavity When the inner cavity of the spherical cavity is in the shape of a spherical ball-shaped ball, it comprises a spherical cavity and a spherical cavity including a spherical core, and the bottom surface of the spherical cavity and the ball A bottom surface of the mesa cavity is matched and connected together, and the connection between the spherical cavity and the spherical cavity is a detachable connection or a fixed connection.
  • the shape of the inner cavity of the spherical resonant cavity may also be a complete spherical shell shape.
  • one ultrasonic transmitting unit is a wave source
  • the outer shape of the spherical resonant cavity formed by the one or more ultrasonic transmitting units may take any shape as long as the shape of the inner cavity of the spherical resonant cavity is spherical or It can be a ball-shaped shell shape including the center of the ball.
  • the spherical cavity may be formed only by a spherical shell-shaped ultrasonic emitting unit, or the spherical shell-shaped cavity may be divided into
  • each of the divided small blocks is an ultrasonic transmitting unit that emits a spherical wave having the same radius, that is, the spherical spherical spherical resonant cavity can also be composed of a plurality of spherical waves having the same radius of emission
  • the ultrasonic emission unit is formed.
  • the ultrasonic transmitting unit can also be made of other types of piezoelectric materials, as long as the condition that the ultrasonic wave emitted by the wavefront is spherical wave is satisfied, for example, a combination of a piezoelectric material that emits plane ultrasonic waves and a focusing lens can be used (constituting one)
  • the lens-focusing ultrasonic transducer unit may be a plurality of lens-focusing ultrasonic transducer units that together form a spherical shell-shaped inner cavity.
  • the distances of the respective focus lenses to the center of the sphere are equal, and the inner cavity of the spherical cavity formed by the inner surfaces of the respective focus lenses is formed into a spherical shell shape or a cut containing a spherical core.
  • Spherical shell shape since this type of ultrasonic transmitting unit can also emit a spherical wave, it also conforms to the conditions of the ultrasonic transmitting unit of the present invention.
  • the ultrasonic transmitting unit needs to satisfy the ultrasonic resonance superposition principle, that is, the diameter of the formed spherical resonant cavity is an integral multiple of the ultrasonic half wavelength.
  • the ultrasonic transducer of this structure can only be used when When the volume is very large, for example, the entire person can be accommodated inside, the lesion can be effectively treated. Therefore, according to the needs of treatment, such as treatment of the human head, the spherical cavity-shaped spherical cavity is preferably used.
  • the shape of the inner cavity includes a spherical cavity (the height of the cavity is larger than the radius of the ball) and a spherical cavity (the height of the cavity is smaller than the radius of the ball), the bottom surface of the spherical cavity and the bottom surface of the spherical cavity Consistently, and connected together, the connection between the spherical cavity and the spherical cavity is a detachable connection or a fixed connection.
  • the ultrasonic wave emitted by the ultrasonic transmitting unit and the reflected The ultrasonic waves form a resonance-enhanced focal region at the center of the sphere.
  • the shape of the inner cavity of the spherical cavity formed by using the above ultrasonic transducer is a spherical spheroidal cavity
  • the ultrasonic transducer is compressed only in a focal region perpendicular to the direction of the acoustic axis
  • the acoustic axis is The focus area in the direction of the center axis of the spherical cavity is not compressed, so the focus gain of the ultrasonic transducer at the center of the sphere relative to the ultrasonic transducer having the shape of the inner cavity as a spherical shell Be weaker.
  • the shape of the spherical cavity of the spherical cavity includes a spherical cavity including a spherical core and two spherical cavities respectively disposed at upper and lower ends of the spherical cavity.
  • the shape of the spherical cavity of the spherical cavity may also include a spherical cavity including a spherical core and two spherical crown cavities respectively disposed at upper and lower ends of the spherical cavity,
  • the bottom surfaces of the two spherical crown chambers respectively coincide with the upper bottom surface and the lower bottom surface of the spherical chamber, and the two sides are connected together, and the connection between the spherical chamber and the two spherical crown chambers is detachably connected. Or a fixed connection.
  • the ultrasonic transmitting unit emits The ultrasonic waves and reflected ultrasound form a resonance-enhanced focal region at the center of the sphere.
  • the two bottom surfaces of the spherical-shaped resonant cavity are parallel, and the distances to the center of the sphere may be equal or unequal, and the specific distance may be designed according to the needs of use. In order to keep the gathering gain at the center of the ball as large as possible, it is preferable that the distance between the two bottom surfaces of the spherical cavity to the center of the sphere is equal.
  • the shape of the inner cavity of the spherical cavity formed by using the above ultrasonic transducer is a spherical spherical cavity
  • the ultrasonic focusing region is only compressed in the circumference, that is, only in the sound propagation plane Compression is performed in all directions, and there is also a certain edge diffraction along the central axis of the ultrasonic transducer. Therefore, the relative gain of the ultrasonic transducer at the center of the sphere is weaker than that of the ultrasonic transducer whose inner cavity is a spherical spherical cavity.
  • the spherical resonator formed above is further provided with a hole for the image monitoring device to pass through.
  • the ultrasonic transmitting unit may be one or more.
  • the ultrasonic transmitting unit constitutes a complete spherical shell-shaped spherical cavity.
  • a plurality of ultrasonic transmitting units in the present invention may also be employed, and different ultrasonic transmitting units may emit ultrasonic waves of different frequencies.
  • the ultrasonic frequencies emitted by the plurality of ultrasonic transmitting units are different, the ultrasonic transmitting units of different frequencies may form an energy superposition at the focus, but the energy superposition is not a coherent superposition, and thus at the focus (the center of the sphere) It is impossible to form a high energy as a coherent superposition, but it is still possible to form an energy superposition at the focus, because this superposition is much higher than that of a single wave source.
  • the spherical ultrasonic waves emitted by the respective ultrasonic transmitting units have a phase difference of 20%, and it is further preferable that the frequencies of the spherical ultrasonic waves emitted by the plurality of ultrasonic transmitting units are both The same, to form a resonance, so that the ultrasonic energy forms a coherent superposition at the center of the ball, so that the ultrasonic energy can be further increased.
  • a spherical resonant cavity is formed. All the ultrasonic waves emitted and reflected in the spherical cavity pass through the center of the sphere, and the ultrasonic energy at the center of the sphere is superimposed in the same phase, so the ultrasonic energy is greatly enhanced, and the aspherical in the spherical cavity
  • the ultrasonic energy at the resonance point is weakened, so that when the human body is treated by the ultrasonic transducer of the present invention, the focus can be ensured to the greatest extent.
  • the lesion tissue at the site receives great ultrasound energy and also ensures the safety of human tissue in non-focus areas.
  • the diffraction mechanism of the ultrasonic transducer of the present invention is similar to the diffraction principle in optics.
  • the ultrasonic transducer of the present invention adopts a spherical spherical spherical cavity including a spherical core, since the open ultrasonic transducer still has a diffraction phenomenon in a circumferential direction perpendicular to the acoustic axis, this direction The length of the upper focusing region is not compressed; when the ultrasonic transducer of the present invention adopts a spherical shell-shaped spherical cavity, when the entire acoustic path is completely closed, no diffraction occurs, and thus the energy at the focal point is maximum.
  • the ultrasonic transducer of the invention solves the problems existing in deep tissue diseases and intracranial ultrasound treatment of the human body, and enables sufficient ultrasonic energy to reach the human body in the case of ensuring human body safety.
  • the tissue is configured to avoid thermal damage caused by the absorption of ultrasound by bone tissue located on the ultrasonic path. Therefore, the ultrasonic transducer of the present invention is particularly suitable for treating deep tissue and intracranial lesions of the body.
  • the ultrasonic transducer of the present invention not only has a large ultrasonic emission area, but also has a large focusing gain, which greatly enhances the energy at the ultrasonic focus and is hardly affected by the operating frequency of the ultrasonic transmitting source.
  • the ultrasonic transducer of the present invention has the following advantages: (1) The size of the focus area of the ultrasonic wave emitted by the ultrasonic transducer of the present invention is hardly affected by the frequency of the ultrasonic transmitting unit, and the utilization is utilized. Low-frequency ultrasound can form coagulative necrosis in the lesion; (2) The length of the ultrasound focused area along its various directions can be effectively compressed, greatly reducing the volume of the focal area and improving the focal area.
  • FIG. 1 is a schematic structural view of a spherical shell-shaped spherical cavity according to Embodiment 1 of the present invention
  • FIG. 2 is a schematic structural view of a spherical shell-shaped spherical resonant cavity according to Embodiment 2 of the present invention
  • FIG. 3 is a spherical shape of a second embodiment of the present invention
  • Schematic diagram of the spherical resonant cavity using an ultrasonic transmitting unit
  • FIG. 4 is a schematic structural view of a spherical spherical cavity of a spherical shape according to Embodiment 2 of the present invention (using a plurality of ultrasonic transmitting units);
  • FIG. 5 is a schematic structural view of a (regular) spherical-type spherical cavity according to Embodiment 3 of the present invention (using an ultrasonic transmitting unit);
  • Embodiment 6 is a schematic structural view of a (regular) spherical-type spherical cavity (parallel to two bottom faces) in Embodiment 3 of the present invention (using a single-layer multiple ultrasonic transmitting unit);
  • Embodiment 7 is a schematic structural view of a (regular) spherical-type spherical cavity (parallel to two bottom surfaces) in Embodiment 3 of the present invention (multiple layers of ultrasonic transmitting units are used);
  • FIG. 8 is a schematic structural view of a (non-regular) spherical-type spherical cavity (the bottom surfaces are not parallel) according to Embodiment 4 of the present invention.
  • FIG. 9 is a schematic structural view of an ultrasonic transducer according to Embodiment 5 of the present invention.
  • Figure 10 is a plan view of the ultrasonic transducer of Figure 9;
  • Figure 11 is a half cross-sectional view of the ultrasonic transducer of Figure 9.
  • 1 Ultrasonic emission unit 10 - spherical shell cavity 11 - spherical crown cavity 12 - spherical cavity 13, 14 a spherical cavity 15 - planar piezoelectric wafer 16 - focusing lens 20 - hole hi - the height of the spherical cavity h2 - the height of the spherical cavity R - the radius of the ball S1 - the upper surface S2 - the lower surface is implemented the way
  • the ultrasonic transducer of the present invention includes one or more ultrasonic transmitting units, the wavefront of the ultrasonic waves emitted by the one or more ultrasonic transmitting units being spherical, and the one or more ultrasonic transmitting units simultaneously having reflected ultrasound Function, the wavefront is a spherical surface having the same radius, the one ultrasonic emitting unit forms a spherical resonant cavity, or the plurality of ultrasonic transmitting units together form a spherical resonant cavity, and the shape of the inner cavity of the spherical resonant cavity is
  • the spherical shell shape is a truncated spherical shape including a spherical core, and a focal region of the one or more ultrasonic transmitting units is a spherical center position of the spherical resonant cavity.
  • the ultrasonic transducer includes an ultrasonic transmitting unit that simultaneously has a function of reflecting ultrasonic waves, and the ultrasonic transmitting unit is a self-focusing ultrasonic transducer unit.
  • the wavefront of the ultrasonic wave emitted by the ultrasonic transmitting unit is a spherical surface with the same radius, and the ultrasonic wave emitted by the ultrasonic transmitting unit is a spherical wave, and the ultrasonic emitting unit forms a spherical resonant cavity, and the inner cavity shape of the spherical resonant cavity is a complete shape.
  • the spherical shell shape thus constitutes a spherical shell-shaped spherical cavity in which the acoustic path is completely closed.
  • the focus area of the spherical shell-shaped spherical cavity is the spherical center position of the spherical shell.
  • the ultrasonic wave emitted from the ultrasonic transmitting unit and the ultrasonic wave emitted or reflected on the opposite surface thereof form a resonance-enhanced focusing area at the center of the sphere.
  • the ultrasonic transmitting unit can be made of various shapes of self-focusing ultrasonic piezoelectric materials.
  • the ultrasonic transducer of the present invention can be directly formed into the spherical shell-shaped cavity 10 as shown in FIG.
  • the outer casing of various shapes may be added outside the cavity of the spherical cavity formed as needed, B, as long as the inner cavity shape of the spherical resonant cavity is ensured to be a complete spherical shell shape.
  • the spherical shell-shaped cavity 10 in this embodiment adopts an opening and closing type so that the article is placed inside the spherical shell-shaped cavity 10, and the specific position of the opening and closing portion can be set according to the actual need of the placed articles. .
  • the ultrasonic transducer in this embodiment is mainly suitable for some medical experiments that can be performed in a closed environment.
  • a stereoscopic organ, or an experimental phantom, etc. is placed in the spherical shell-shaped cavity 10 of the ultrasonic transducer, and then the entire spherical cavity 10 is sealed to start treatment or experiment. After treatment or experiment, open the spherical cavity 10 to see the effect of the treatment or experiment, and depending on the treatment or experiment, As a guide for clinical use and so on.
  • the ultrasonic transducer can also be used to treat a human body when the volume of the spherical shell 10 is large, such as when the entire human body can be accommodated within the spherical cavity 10.
  • the shape of the inner cavity of the spherical cavity formed by the ultrasonic transducer is also a complete spherical shell shape, which is different from the embodiment 1 in that the spherical shell spherical resonance
  • the cavity is not formed by only one ultrasonic emitting unit, and the inner cavity of the spherical shell-shaped spherical cavity is composed of a spherical cavity 12 (shown in FIGS. 3 and 4) and a spherical cavity 11, which is composed of a ball.
  • the bottom surface of the missing cavity 12 coincides with the bottom surface of the spherical cavity 11 and is connected together, and the connection between the spherical cavity 12 and the spherical cavity 11 is detachably connected.
  • the height hi of the spherical cavity 11 is smaller than the radius R of the ball, and the height h2 of the spherical cavity 12 is greater than the radius R of the ball.
  • a ball-shaped cavity 12 is further provided with an image monitoring device for entering.
  • the hole 20, of course, the hole 20 can also be opened on the spherical cap-shaped cavity 11.
  • the spherical cavity 12 can be formed by an ultrasonic emitting unit 1 (as shown in FIG. 3). For the sake of simplicity in manufacturing, it can also be formed by a plurality of ultrasonic transmitting units together (as shown in FIG. 4). Show).
  • the spherical cavity 11 may be formed by one ultrasonic transmitting unit 1, or may be formed by a plurality of ultrasonic transmitting units.
  • the one or more ultrasound transmitting units employ a self-focusing ultrasound transducer unit having a reflected ultrasound function.
  • the wavefront of the ultrasonic waves emitted by the one or more ultrasonic transmitting units is a spherical surface of the same radius.
  • the ultrasonic waves emitted by the ultrasonic transmitting units have a magnitude difference of 20%, preferably, the ultrasonic waves emitted by the plurality of ultrasonic transmitting units
  • the frequency is the same.
  • the spherical cavity 12 is adapted to treat a human head.
  • the human head enters the spherical cavity 12, and the ultrasonic wave and the reflected ultrasonic wave emitted by the ultrasonic emitting unit form a resonance-enhanced focusing area at the center of the ball, so that the human body lesion is at the center of the ball, and then the composition is started.
  • the ultrasound emitting unit of the spherical cavity 12 can begin treatment.
  • the spherical shaped cavity 12 can also form an ultrasonic transducer having a spherical cavity shaped spherical cavity in its inner cavity. In the ultrasonic transducer, it can be selectively added to the external cavity of the cavity. It is available in various shapes (no housing is available).
  • the shape of the inner cavity of the spherical cavity formed by the ultrasonic transducer is a ball-shaped shell shape including a spherical core, and the spherical cavity-shaped spherical cavity of the spherical-shaped spherical cavity
  • the inner cavity is a regular spherical cavity 13 .
  • the upper bottom surface S1 and the lower bottom surface S2 of the spherical cavity 13 are parallel, and the distance from the upper bottom surface S1 to the center of the sphere is equal to the distance from the lower bottom surface S2 to the spherical center O.
  • the number of the ultrasonic transmitting units 1 constituting the spherical cavity 13 may be one (as shown in FIG. 5), or may be a single-layer multiple ultrasonic transmitting unit (as shown in FIG. 6), or Multiple layers of multiple ultrasound transmitting units (as shown in Figure 7).
  • the one or more ultrasound transmitting units employ a self-focusing ultrasound transducer unit having a reflective ultrasound function.
  • the Z-axis direction shown in Fig. 5 is the acoustic axis direction of the turret-shaped cavity 13, and the Z-axis coincides with the central axis of the spheroid-shaped cavity 13.
  • the ultrasonic waves emitted by the plurality of ultrasonic transmitting units have the same frequency.
  • the wavefront of the ultrasonic waves emitted by the ultrasonic transmitting unit is a spherical surface having the same radius.
  • the ultrasonic transducer in this embodiment is suitable for treating the trunk or limbs of the human body.
  • the torso portion or limb portion of the human body is first passed through the spheroidal cavity 13, and the lesion is placed at the center of the ball, and the ultrasound emitting unit is activated to start treatment.
  • the shape of the inner cavity of the spherical resonant cavity formed by the ultrasonic transducer is a ball-shaped shell shape including a spherical core, and the inner cavity of the spherical spherical cavity resonant cavity is adopted.
  • the upper bottom surface S1 and the lower bottom surface S2 of the spherical cavity 14 are not parallel.
  • the distance from the upper surface S1 to the center 0 is equal to the distance from the lower surface S2 to the center 0.
  • the number of the ultrasonic transmitting units 1 constituting the spherical cavity 14 may be one, or may be a single layer of a plurality of ultrasonic transmitting units, or may be a plurality of layers of ultrasonic transmitting units.
  • the one or more ultrasound transmitting units employ a self-focusing ultrasound transducer unit having a reflected ultrasound function.
  • the Z-axis direction shown in Fig. 8 is the acoustic axis direction of the spherical cavity 14, and the Z-axis coincides with the central axis of the spherical cavity 14.
  • the ultrasonic waves emitted by the plurality of ultrasonic transmitting units have the same frequency.
  • the wavefront of the ultrasonic wave emitted by the ultrasonic transmitting unit is A sphere with the same radius.
  • the ultrasonic transducer in this embodiment is suitable for treating diseases such as uterine fibroids.
  • diseases such as uterine fibroids
  • an ultrasonic transducer of such an irregular spherical spherical cavity in this embodiment can be employed.
  • the present embodiment differs from Embodiment 3 in that the ultrasonic transmitting unit in the ultrasonic transducer is formed by a combination of a piezoelectric material that emits planar ultrasonic waves and a focusing lens, that is, the ultrasonic transmitting unit employs a lens focusing ultrasonic transducer unit.
  • the spherical cavity is composed of four planar piezoelectric wafers 15 and four focusing lenses 16, that is, a focusing lens 16 is attached to each of the planar piezoelectric wafers 15.
  • the ultrasonic waves emitted by the four lens-focused ultrasonic transducer units are also spherical waves, and the wavefronts of the ultrasonic waves emitted by them are also spherical surfaces having the same radius.
  • the inner surfaces of the four focusing lenses 16 are all part of a spherical surface, and the distances of the respective focusing lenses to the center of the sphere are the same, they are collectively joined together to form a spherical cavity including a spherical core (of course, it can also be formed into a spherical shell shape).
  • a cavity or a spherical cavity that is, the inner cavity of the spherical cavity formed by the ultrasonic transducer is in the shape of a ball-shaped dome containing a spherical core, and the cavity of the spherical cavity of the spherical cavity
  • the body adopts a spherical cavity.

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Abstract

本发明公开了一种超声换能器，其包括一个或多个超声发射单元，所述一个或多个超声发射单元所发射的超声波的波阵面为半径相同的球面，该一个或多个超声发射单元同时具有反射超声的功能，所述一个超声发射单元形成一个球面共振腔/或所述多个超声发射单元共同构成一个球面共振腔，所述球面共振腔的内腔体的形状为球壳形或者为包含球心在内的截球壳形，所述一个或多个超声发射单元所发射的超声波的聚焦区域为所述球面共振腔的球心。本发明超声换能器不仅超声发射面积大，而且聚焦增益很大，极大地增强了超声波焦点处的能量，且几乎不受超声发射源工作频率影响。

Description

一种超声换能器 技术领域
本发明属于超声治疗技术领域， 具体涉及一种超声换能器。 背景技术
利用超声进行疾病治疗时， 由于大量超声能量在传输路径上的损失， 使 得在病灶处聚焦的超声强度很低， 无法达到临床所需的治疗效果， 因此对于超 声治疗设备而言， 目前需要解决的棘手技术难点就是如何尽量减少超声在传播 路径上所发生的严重衰减以及如何提高治疗部位超声强度的问题。
现有技术中解决上述技术问题的方式一般是通过对超声换能器的设计来 达到的。 现有的超声换能器， 通常超声能量聚焦区域的大小和强度与该超声换 能器的发射面积和频率相关， 发射面积越大， 则聚焦区域聚集的超声能量就越 大， 而超声换能器的工作频率越高， 则发射的超声波波长就越短， 进而聚焦区 域就越小， 从而超声强度就越高。
为了增大超声换能器的发射面积， 美国专利 US2006/0058678A1中揭露了 一种超声换能器， 它将超声发射源固定到一个环形的支持体上， 以增大超声波 的发射面积。为了避免超声发射源的互相影响，设计时采用了这样的技术方案： 让每个超声发射源相对的环面为缺口，相对于采用单个超声发射源的换能器而 言， 该超声换能器提高了换能器的聚焦增益。 但由于该超声换能器在超声发射 源相对的环面上设置缺口， 使环面上超声波发射源的有效发射面积减少， 且缺 口会导致超声能量的散失， 降低了这种治疗头作为一个环形整体的聚焦区域能 量， 对增加超声换能器的聚焦能力不利。 同时， 该技术方案只是简单的增加 了超声换能器的发射面积， 使之在焦点处进行能量的叠加， 在频率较低时， 由 于波长较长， 超声波的聚焦能力就不好， 聚焦区域较大， 因而该聚焦区域的超 声强度就较弱， 在进行超声治疗时， 不能快速有效的形成靶区的凝固性坏死； 而如果采用较高的频率进行工作时， 由于超声在组织内的穿透性不好， 在对人 体深部组织等进行超声治疗中，超声波需要经过人体皮肤、骨组织、含气组织、 神经组织等组织后才能达到聚焦位置， 而上述组织对传输的超声波具有吸收、 反射等作用， 这不但造成了聚焦区域能量的减少和弥散， 而且组织吸收超声波 后会造成这些组织温度上升， 当超声换能器的发射功率很大时， 因这些组织的 温度升高， 可能造成组织意外损伤。 另外， 由于人体组织对超声波有很大的非 线性效应， 高强度的超声波在人体组织中传输， 将有很大一部分超声波转化为 超声波的高次谐波， 而被组织吸收掉， 这时如果继续增大换能器的超声发射功 率， 将产生更大的非线性效应， 使得增大的超声波能量不能有效的传输到所预 期的聚焦区域， 形成声饱和现象， 从而影响超声波的聚焦。
可见， 现有技术通过简单的增加超声换能器的发射面积和进行能量的叠 加并不能有效的解决上述技术问题。
实际上， 超声换能器发射源相对面上的发射和反射是可以用来增强聚焦 增益的， 如本申请人之前申请的中国专利 （公开号为 CN 101140354A) 中公开 了一种谐振式超声换能器， 该谐振式超声换能器采用相对设置的超声换能器和 超声反射单元构成谐振腔， 由于超声反射单元相当于一个超声换能器， 因而该 谐振腔实际上相当于由两个对称设置的超声换能器构成，通过此谐振腔内超声 波的共振，使得超声波的聚焦区域在声轴线方向上的长度比仅使用单个超声换 能器时变短 （两个同频率的超声波相对而来， 他们在相遇的区域会发生干涉， 产生干涉时在中心点同相， 而在其它点是非同相的， 所以两者的叠加就会造成 偏离中心分布弱， 造成超声焦域缩短） ， 使能量更集中， 聚焦增益得到极大提 高。 采用该谐振腔换能器的工作模式， 可以在不增大超声换能器发射面积的情 况下， 使换能器聚焦区域的增益更大。
但采用这种结构的超声换能器也存在有很多不足： 第一， 两换能器所构 成的谐振腔不是一个环形封闭的球面， 不能形成有效的声共振， 仍然有一部分 能量会从相对设置的两个换能器中间的开口部分逸出， 无法将换能器发射的超 声波能量充分利用起来； 第二， 由于两个换能器是相对设置的， 两者之间没有 固定连接， 这种结构容易导致两个换能器偏离共振条件， 因而需要保证在两个 换能器发射超声波的超声波路径上不能受到其他因素的干扰， 否则这两个相对 设置的换能器间可能会无法形成所需的共振腔，无法在聚焦区域产生足够的增 益， 或者导致其它聚焦区域的形成从而损害其它的正常组织； 第三， 其聚焦区 域长度只是在共振腔的声轴线方向上得到压縮，在偏离共振腔声轴线的其它方 向上的聚焦区域长度并没有得到压缩， 也就是说所形成的聚焦区域只有在超声 波声轴线方向上的长度得到了压缩， 聚焦区域体积并没有足够的减小； 第四， 该超声换能器的聚焦区域大小仍受频率影响，无法做到在低频的工作条件下超 声也有很好的组织穿透性， 从而解决在传输路径上能量严重损失的技术问题； 第五， 超声换能器的发射面积不够大。 发明内容
本发明要解决的技术问题就是针对现有技术所存在的上述不足， 提供一 种超声发射面积大， 并且超声波的聚焦能力几乎不受超声发射源工作频率影响 的超声换能器。
解决本发明技术问题所采用的技术方案是该超声换能器包括一个或多个 超声发射单元，所述一个或多个超声发射单元所发射的超声波的波阵面为半径 相同的球面， 该一个或多个超声发射单元同时具有反射超声的功能， 所述一个 超声发射单元形成一个球面共振腔 /或所述多个超声发射单元共同构成一个球 面共振腔，所述球面共振腔的内腔体的形状为球壳形或者为包含球心在内的截 球壳形，所述一个或多个超声发射单元所发射的超声波的聚焦区域为所述球面 共振腔的球心。
本发明中， 由于超声发射单元所形成的球面共振腔的内腔体的形状为球 壳形或者为包含球心在内的截球壳形，且整个球面共振腔的腔体表面既是超声 波的发射面又是超声波的反射面， 从而使有效的超声发射面积得到增大， 并且 能够增加反射的次数。 同时， 每个超声发射单元的波阵面上的球面超声波按原 发射路径的反方向反射回来后， 由于反射的超声波与发射的超声波频率相同， 这两列超声波在球面共振腔内部形成共振，又由于这两列超声波到达球心处的 时间相同， 整个球面共振腔的腔体内产生多个共振点， 当球面共振腔内的介质 对超声波吸收很小（通常在超声波的频率较低时，介质对超声波的吸收很小）， 且超声发射单元具有良好的反射超声的性能时， 则超声发射单元发出的超声波 可以在此球面共振腔内发生多次反射，从而使超声波在此球面共振腔内多次发 生共振。 由于该球面共振腔的球心处也是共振点， 从球面共振腔腔体表面发出 的超声波和其相对面上反射的超声波在球心处形成了一个共振增强的聚焦区 域， 因此也就提高了球心处的超声波强度，大大提高了超声波的利用率。并且， 由于一个或多个超声发射单元所发射的超声波能量以及反射的超声波能量都 集中于球心位置时， 球心处再经过多次共振加强， 能量得到成倍的增长， 从而 进一步加强了球心位置的共振， 也就进一步提高了聚焦区域的能量。 而对于位 于非球心处的共振加强点而言， 由于其共振加强的次数相当有限， 因此， 此球 面共振腔内的非球心位置处的超声能量相对于球心处的超声能量是相当低的， 这样， 当治疗部位处于球心位置时， 可有效避免对非期望治疗部位的损伤。 如果采用现有的常规超声换能器直接聚焦对人体进行治疗， 设其焦点处 的声压为 P， 声强为 I； 同样， 采用本发明超声换能器对人体进行治疗， 设超 声发射单元所发射超声波的频率与采用常规超声换能器进行治疗时所采用的 频率相同， 假设本发明超声换能器对超声的衰减为 10%左右， 那么经过一次反 射后， 其超声波的声压衰减为原来的 0. 9倍左右， 即声压衰减为 0. 9P, 经过两 次衰减后衰减为原来的 0. 81倍左右 （先假设只经过两次反射， 当然实际的反 射次数远不止两次） ， 即声压衰减为 0. 81P, 此时在球心处叠加后的声压为 P+0. 9P+0. 81P = 2. 71P, 由于超声波发射和反射过程各进行两次 （超声发射单 元同时具有超声发射和超声反射的功能） ， 因而球心处总的声压为 2 X 2. 71P
= 5. 42P, 而声强与声压成平方关系， 因此聚焦区域球心处的声强变为 5. 4221 = 29. 37641。 因此， 在只计算了超声波发生两次反射的情况下， 本发明超声换 能器就达到了相当于常规超声换能器接近 30倍的能量。 而在实际应用的过程 中， 随着反射次数的增加， 衰减量的进一步减小， 其聚焦能量还会更高。 从这 里可看出本发明超声换能器的聚焦处的超声能量要远远高于现有的超声换能 器。
本发明超声换能器所形成的球面共振腔可以为球壳形或者为一个包含球 心在内的截球壳形。 当球面共振腔的内腔体的形状为球壳形时， 它是一个声路 完全闭合 （或者也可以称为 "声路密闭" ） 的球面共振腔， 超声波只在此共振 腔内进行传播， 而不会发散到共振腔的腔体外部。 当球面共振腔的内腔体的形 状为包含球心在内的截球壳形时，所谓包含球心在内是指该球面共振腔所形成 的内腔体的形状在与其中心轴线垂直且过球心的圆周方向上是声路闭合的， 即 构成该内腔体的曲线中包括有过球心的圆周曲线， 这样就保证了该球面共振腔 在与其中心轴线垂直的圆周方向上形成声路闭合 （或者也可以称为 "声路密 闭"， 即在此圆周方向上没有声波泄露的声场分布模式， 使得此圆周方向不发
' 生衍射， 可以实现很好的聚焦） 。 因此， 相对于以往的超声换能器 （比如公开 号为 CN 101140354A的中国专利） 而言， 本发明超声换能器能够防止全部或者 绝大部分的超声波能量从共振腔中逸出。
由于聚焦超声换能器的超声能量聚焦区域是由超声换能器振动发射面的 边缘衍射引起的， 传统的聚焦超声换能器由于超声波发射面的边缘效应， 会引 起超声能量聚焦区域分散， 并且随着超声换能器工作频率的减小， 边缘效应的 影响会变大， 从而产生超声聚焦能力减弱的现象 （即聚焦区域会增大） ， 所以 在进行超声治疗时， 要使治疗部位形成凝固性坏死， 一般的超声换能器所需要 的工作频率比较高， 目前通常的频率范围为 0. 8匪 Z— 1(MHZ。 而本发明超声换 能器所形成的球面共振腔中， 由于其在超声传播的一个或多个方向上声路是密 闭的， 因而在聚焦区域的圆周方向上不会产生衍射现象， 也就不会有随超声频 率的减小而引起超声聚焦能力减少这种现象发生， 这就使得本发明的焦域大小 几乎不受超声换能器发射频率的影响（当然， 对于球面共振腔的内腔体形状为 包含球心在内的截球壳形的超声换能器而言，其只保证了超声波聚焦区域在经 过球心且与声轴线垂直的圆周内进行了压缩， 即只是在声传播平面的各个方向 上进行了焦域的压縮， 因此在沿其中心轴线方向上还存在着一定的边缘衍射现 象） ， 因而本发明中超声发射单元的工作频率的下限范围值相对于现有的超声 换能器中的超声发射单元而言可以适当选小， 其工作频率的范围为 20kHz— 10MHz , 优选工作频率范围为 0. 1MHz— 0. 8MHz。
由于本发明超声换能器的聚焦能力要远强于现有的超声换能器， 因此即 使在低频的情况下， 比如频率仅为 20kHz的情况下， 本发明超声换能器也可以 有效地工作， 以实现对人体的有效治疗， 而传统的超声换能器根本不可能在如 此低的频率下产生高声场。 这样， 在对一些具有含气组织、 骨头或有其他组织 遮挡的组织器官进行治疗时， 由于本发明工作频率低， 组织温升很小， 所以可 以对人体进行安全、 有效的治疗。 此外， 由于在实际治疗过程中超声反射的次 数是有限的， 而本发明超声换能器中的超声发射单元同时又是超声反射单元
(超声发射单元同时具有反射超声的功能） ， 其聚焦能力强， 因而能在低频的 条件下工作， 而降低超声发射单元的工作频率， 还有利于增加超声反射的次数 (因为频率越低， 组织对超声的吸收越小， 则反射发生的次数越多） ， 从而可 进一步增加聚焦区域处 （球心） 的超声强度。
在设计本发明球面共振腔时， 需要保证发射球面波的超声发射单元所形 成的球面共振腔满足超声共振叠加原理， 即球面共振腔的直径为所发射的超声 波半波长的整数倍。
本发明中， 当球面共振腔的内腔体的形状为包含球心在内的截球壳形时， 所述包含球心在内的截球壳形内腔体可以为球缺截球壳形内腔体（腔体的高度 大于球半径） 或球台截球壳形内腔体。
当所述球面共振腔的内腔体形状为包含球心在内的球台截球壳形时， 可 以采用下面几种形式：
一种是， 该截球壳形内腔体的上底面 S1与下底面 S2平行， 上底面到球 心的距离与下底面到球心的距离不相等。
一种是， 该截球壳形内腔体的上底面 S1与下底面 S2平行， 且上底面到 球心的距离与下底面到球心的距离相等，这种形状可以保持在球心处的聚集增 益尽量大。
当然， 在实际使用时， 若不能采用上述两种球台截球壳形内腔体的球面 共振腔进行治疗时（比如在进行子宫肌瘤等疾病治疗时） ， 球面共振腔的内腔 体的形状也可以采用不规则形状的球台截球壳形， 此时该包含球心在内的球台 截球壳形内腔体的上底面与下底面不平行，其上底面到球心的距离与下底面到 球心的距离可以相等， 也可以不相等。
当球面共振腔的内腔体形状为球缺截球壳形时， 其包括一个球冠形腔和 一个包含有球心在内的球台形腔，所述球冠形腔的底面与所述球台形腔的一个 底面相吻合， 且连接在一起， 所述球冠形腔和球台形腔之间的连接为可拆卸式 连接或固定连接。
所述球面共振腔的内腔体形状也可以是一个完整的球壳形。
本发明中， 一个超声发射单元即为一个波源， 一个或多个超声发射单元 所形成的球面共振腔的外壳形状可以采用任意形状，只要保证球面共振腔的内 腔体的形状为球壳形或者为包含球心在内的截球壳形即可。当所制作的球面共 振腔的内腔体的形状为一个完整的球壳形时， 该球面共振腔可以仅由一个球壳 形的超声发射单元形成， 也可以将此球壳形的腔体分割为多个小块， 则分割下 来的每一小块都是一个可发射半径相同的球面波的超声发射单元， 也就是说， 该球壳形的球面共振腔也可以由多个发射半径相同球面波的超声发射单元形 成。 超声发射单元还可以采用其他类型的压电材料制成， 只要满足其波阵面发 射的超声波为球面波的条件即可， 比如可以采用发射平面超声波的压电材料与 聚焦透镜的组合 （构成一个透镜聚焦超声换能器单元） ， 该透镜聚焦超声换能 器单元可以采用多个， 共同形成一个球壳形内腔体。 其中， 各个聚焦透镜到球 心的距离相等，且各聚焦透镜的内表面拼合成一体后所形成的球面共振腔的内 腔体的形状为一个球壳形或者为一个包含球心在内的截球壳形， 由于这种类型 的超声发射单元也可以发射球面波， 那么它也符合本发明超声发射单元的条 件。 在设计球面共振腔时， 超声发射单元需要满足超声共振叠加原理， 即所 形成的球面共振腔的直径为超声波半波长的整数倍。
当上述球面共振腔的内腔体形状为完整的球壳形时， 虽然可以最大限度 的使超声能量在球心处得到增强， 但是在实际治疗需要中， 这种结构的超声换 能器只有当其体积非常大时， 比如可以容纳整个人在其内部时， 才能有效的对 病灶进行治疗， 因此根据治疗的需要， 比如对人体头部进行治疗时， 优选所述 球壳形的球面共振腔的内腔体形状包括一个球缺形腔 （腔体的高度大于球半 径）和一个球冠形腔 （腔体的高度小于球半径） ， 所述球缺形腔的底面与球冠 形腔的底面相吻合， 且连接在一起， 所述球缺形腔和球冠形腔之间的连接为可 拆卸式连接或固定连接。当所述球缺形腔和球冠形腔之间的连接为可拆卸式连 接时， 在对人体头部进行治疗时， 可以只使用球缺形腔， 超声发射单元所发射 的超声波和反射的超声波在球心处形成共振增强的聚焦区域。
在使用上述超声换能器所形成的球面共振腔的内腔体形状为球缺形球面 共振腔时， 由于超声换能器只是在垂直于声轴线方向的聚焦区域进行了压缩， 而在声轴线 （即球面共振腔的中心轴线）方向上的聚焦区域没有压縮， 所以相 对于采用内腔体形状为球壳形的超声换能器而言， 该超声换能器在球心处的聚 焦增益要弱一些。
或者所述球壳形的球面共振腔内腔体的形状包括一个包含有球心在内的 球台形腔和分设于所述球台形腔上、 下端的两个球冠形腔。
所述球壳形的球面共振腔内腔体的形状也可以包括一个包含有球心在内 的球台形腔和分设于所述球台形腔上、 下两端的两个球冠形腔， 所述两个球冠 形腔的底面分别与球台形腔的上底面和下底面相吻合， 且两两连接在一起， 所 述球台形腔与两个球冠形腔之间的连接为可拆卸式连接或固定连接。当所述球 台形腔与两个球冠形腔之间的连接为可拆卸式连接时，在对人体"躯干、四肢" 进行治疗时， 可以只使用上述球台形腔， 超声发射单元所发射的超声波和反射 的超声波在球心处形成共振增强的聚焦区域。
优选上述球台形共振腔的两底面平行， 且到球心的距离可以相等， 也可 以不相等， 具体的距离可以根据使用的需要进行设计。 为了保持在球心处的聚 集增益尽量大， 优选该球台形腔的两个底面到球心的距离相等。
在使用上述超声换能器所形成的球面共振腔的内腔体形状为球台形球面 共振腔时， 由于超声波聚焦区域只是在圆周内进行压縮， 即只是在声传播平面 的各个方向上进行了压缩，在沿超声换能器中心轴线方向还存在着一定的边缘 衍射。 所以相对于内腔体形状为球缺形球面共振腔的超声换能器而言， 其在球 心处的聚焦增益要更弱一些。
优选的是， 上述所形成的球面共振腔上还开有可供图像监控设备通过的 孔。
本发明超声换能器中， 超声发射单元可为一个或多个。 当采用一个超声 发射单元时， 该超声发射单元就构成了一个完整的球壳形球面共振腔。
本发明中的超声发射单元也可以采用多个， 各个不同的超声发射单元可 以发射不同频率的超声波。当多个超声发射单元所发射的超声波频率各不相同 时， 各个不同频率的超声发射单元虽然都可以在焦点处形成能量叠加， 但这种 能量叠加不是相干叠加， 因而在焦点处（球心处）就不能形成如相干叠加那样 高的能量， 但是还是可以在焦点处形成能量叠加， 因为这种叠加方式相对于采 用单个波源而言， 其发射能量还是要高的多。 为了提高聚焦处的超声能量和形 成稳定的超声共振， 优选各个超声发射单元所发射的球面超声波频率相差在 20%的范围内， 进一步优选所述多个超声发射单元所发射的球面超声波的频率 均相同， 以形成共振， 使超声能量在球心处形成相干叠加， 从而可进一步提高 超声能量。
当本发明超声换能器中的超声发射单元采用一个或者采用频率相同的多 个时， 形成一个球面共振腔。 在此球面共振腔中所发射和反射的全部超声波都 经过球心， 且球心处的超声能量都为同相叠加， 因而超声能量得到了极大的加 强， 而对于此球面共振腔中的非球心处的共振点而言， 由于超声能量的叠加为 非同相叠加， 因而该共振点处的超声能量减弱， 因而在利用本发明超声换能器 对人体进行治疗时， 可以最大程度地保证处于焦点处的病灶组织接收到极大的 超声能量， 同时也能保证处于非焦点处的人体组织的安全。
本发明超声换能器的衍射机理与光学中衍射原理类似。 当本发明超声换 能器采用包含球心在内的截球壳形球面共振腔时， 由于此开放式的超声换能器 在垂直于声轴线的圆周方向上还是有衍射现象发生，所以此方向上聚焦区域的 长度没有得到压縮； 当本发明超声换能器采用球壳形球面共振腔时， 此时整个 声路完全闭合则没有衍射发生， 因而焦点处能量最大。
本发明超声换能器很好地解决了人体深部组织疾病和颅内超声治疗所存 在的问题， 在保证人体安全的情况下， 使得有足够的超声波能量能到达人体深 部组织， 并避免了位于超声路径上的骨组织对超声的吸收而引起的热损伤， 因 此本发明超声换能器特别适用于对身体深部组织及颅内病灶进行治疗。
本发明超声换能器不仅超声发射面积大， 而且聚焦增益很大， 极大地增 强了超声波焦点处的能量， 且几乎不受超声发射源工作频率影响。
本发明超声换能器与现有的超声换能器相比， 具有如下优点： （1 ) 本发 明超声换能器所发射的超声波的聚焦区域的大小几乎不受超声发射单元频率 的影响， 利用低频超声波就可以很好的在病灶内形成凝固性坏死； （2) 超声 波的聚焦区域沿其各个方向上的长度都可以得到有效压縮， 大大地减小了聚焦 区域的体积， 提高了聚焦区域的超声波强度； （3 ) 通过利用超声波的共振来 加强聚焦区域处的超声波强度， 而无需加大超声波的发射功率， 因而可以避免 非聚焦区域处的超声强度增大， 保证了治疗部位以外其他部位的安全性。 附图说明
图 1为本发明实施例 1中球壳形球面共振腔的结构示意图； 图 2为本发明实施例 2中球壳形球面共振腔的结构示意图； 图 3为本发明实施例 2中球缺形球面共振腔的结构示意图 （采用一个 超声发射单元） ；
图 4为本发明实施例 2中球缺形球面共振腔的结构示意图 （采用多个 超声发射单元） ；
图 5为本发明实施例 3中（规则）球台形球面共振腔的结构示意图（采 用一个超声发射单元） ；
图 6为本发明实施例 3中 （规则） 球台形球面共振腔 （两底面平行） 的结构示意图 （采用单层多个超声发射单元） ；
图 7为本发明实施例 3中 （规则） 球台形球面共振腔 （两底面平行） 的结构示意图 （采用多层多个超声发射单元） ；
图 8为本发明实施例 4中 （非规则） 球台形球面共振腔 （两底面不平 行） 的结构示意图；
图 9为本发明实施例 5中超声换能器的结构示意图；
图 10为图 9中超声换能器的俯视图；
图 11为图 9中超声换能器的半剖视图。
图中： 1一超声发射单元 10—球壳形腔 11一球冠形腔 12—球缺形腔 13、 14一球台形腔 15—平面压电晶片 16—聚焦透镜 20—孔 hi—球冠形 腔的高度 h2—球缺形腔的高度 R—球半径 S1—上底面 S2—下底面 具体实施方式
下面结合附图和实施例对本发明进一步作详细说明。
本发明中的超声换能器包括一个或多个超声发射单元， 所述一个或多个 超声发射单元所发射的超声波的波阵面为球面， 该一个或多个超声发射单元同 时具有反射超声的功能， 其波阵面为半径相同的球面， 所述一个超声发射单元 形成一个球面共振腔， 或所述多个超声发射单元共同构成一个球面共振腔， 所 述球面共振腔内腔体的形状为球壳形或者为一个包含球心在内的截球壳形，所 述一个或多个超声发射单元的聚焦区域为所述球面共振腔的球心位置。
以下的实施例为本发明的非限定性实施例。
实施例 1 :
本实施例中， 超声换能器包括一个超声发射单元， 该超声发射单元同时 具有反射超声波的功能， 且该超声发射单元为自聚焦超声换能器单元。 所述超 声发射单元所发射的超声波的波阵面为半径相同的球面，其所发射的超声波为 球面波， 该超声发射单元形成一个球面共振腔， 该球面共振腔的内腔体形状为 一个完整的球壳形， 从而构成一个声路完全闭合的球壳形球面共振腔。 该球壳 形球面共振腔的聚焦区域为所述球壳体的球心位置。
本发明超声换能器中， 超声发射单元所发射的超声波和其相对面上发射 或反射的超声波在球心处形成共振增强的聚焦区域。
其中， 超声发射单元可以由各种形状的自聚焦超声压电材料制成， 为了 方便制作，本发明中的超声换能器可以直接制成如图 1所示的球壳形腔 10， 当 然也可以根据需要在所形成的球面共振腔的腔体外部增加各种形状的外壳， B , 只要保证该球面共振腔的内腔体形状为完整的球壳形即可。
本实施例中的球壳形腔 10采用开合式， 以使得将物品放入所述球壳形腔 10的内部， 其开合处的具体位置可以根据实际需要放入的物品的情况来设定。
本实施例中的超声换能器主要适用于一些能够在密闭环境下进行的医学 实验。 比如先将立体器官， 或者实验用的体模等放入该超声换能器的球壳形腔 10内， 然后密封整个球壳形腔 10就可以开始进行治疗或实验。 治疗或实验结 束后， 打开球壳形腔 10， 査看治疗或实验的效果， 并根据治疗或实验的情况， 作为临床使用的指导等等。
当该球壳形腔 10的体积较大时，比如当可以容纳整个人体在球壳形腔 10 之内时， 该超声换能器也可以用于对人体进行治疗。
实施例 2:
如图 2所示， 本实施例中， 超声换能器所形成的球面共振腔的内腔体形状 也为一个完整的球壳形， 其与实施例 1的区别在于， 该球壳形球面共振腔不是 仅由一个超声发射单元形成，该球壳形球面共振腔的内腔体由一个球缺形腔 12 (如图 3、 4所示） 和一个球冠形腔 11共同构成， 所述球缺形腔 12的底面与 球冠形腔 11 的底面相吻合， 且连接在一起， 所述球缺形腔 12和球冠形腔 11 之间的连接为可拆卸式连接。
其中， 球冠形腔 11的高度 hi小于球半径 R， 球缺形腔 12的高度 h2大 于球半径 R。
为了便于对靶区进行定位， 对治疗过程进行监控以及进行及时的疗效评 价， 本实施例中， 如图 3、 4所示， 球缺形腔 12上还开有一个用于图像监控设 备进入的孔 20， 当然， 孔 20也可开设在球冠形腔 11上。
本实施例中，球缺形腔 12可以由一个超声发射单元 1形成（如图 3所示）， 为了制作时工艺上的简单， 也可以由多个超声发射单元共同拼合构成 （如图 4 所示） 。 同理， 球冠形腔 11可以由一个超声发射单元 1形成， 也可以由多个 超声发射单元共同拼合构成。所述一个或多个超声发射单元采用具有反射超声 波功能的自聚焦超声换能器单元。所述一个或多个超声发射单元所发射的超声 波的波阵面为半径相同的球面。
上述采用多个超声发射单元的球缺形腔 12中， 各超声发射单元所发射的 超声波频率的大小相差在 20%的范围之内，优选的是，所述多个超声发射单元 所发射的超声波频率相同。
本实施例中， 球缺形腔 12适合于对人体头部进行治疗。 当对人体头部进 行治疗时， 只使用球缺形腔 12。 首先使人体头部进入该球缺形腔 12内， 由于 超声发射单元所发射的超声波和反射的超声波在球心处形成共振增强的聚焦 区域， 因此使人体病灶处于球心位置处， 再启动构成该球缺形腔 12的超声发 射单元， 即可开始进行治疗。
上述球缺形腔 12事实上也可以独自构成一个内腔体形状为球缺形球面共 振腔的超声换能器， 在该超声换能器中， 可以根据需要选择在其腔体的外部加 设各种形状的外壳 （不加设外壳也可） 。
实施例 3 :
如图 5、 6、 7所示， 本实施例中， 超声换能器所形成的球面共振腔的内 腔体的形状为包含球心的截球壳形， 该截球壳形球面共振腔的内腔体采用一个 规则的球台形腔 13。
本实施例中， 该球台形腔 13的上底面 S1和下底面 S2平行，且上底面 S1 到球心的距离与下底面 S2到球心 O的距离相等。
本实施例中，构成该球台形腔 13的超声发射单元 1的数目可以是一个（如 图 5所示） ， 也可以是单层多个超声发射单元 （如图 6所示） ， 也可以是多层 多个超声发射单元（如图 7所示） 。 所述一个或多个超声发射单元采用具有反 射超声波功能的自聚焦超声换能器单元。 其中， 图 5中所示的 Z轴方向为该球 台形腔 13的声轴线方向， Z轴与该球台形腔 13的中心轴线重合。
当该球台形腔 13由多个超声发射单元拼合形成时， 所述多个超声发射单 元所发射的超声波的频率相同。所述超声发射单元所发射的超声波的波阵面为 半径相同的球面。
本实施例中的超声换能器适合于对人体的躯干或四肢进行治疗。 当对人 体的躯干或四肢进行治疗时， 首先将人体的躯干部分或四肢部分穿过该球台形 腔 13，并使病灶处于其球心位置处，再启动超声发射单元，即可开始进行治疗。
实施例 4:
如图 8所示， 本实施例中， 超声换能器所形成的球面共振腔的内腔体的 形状为包含球心的截球壳形， 该截球壳形球面共振腔的内腔体采用一个不规则 的球台形腔 14。
本实施例中， 该球台形腔 14的上底面 S1和下底面 S2不平行。 且上底面 S1到球心 0的距离与下底面 S2到球心 0的距离相等。
本实施例中， 构成该球台形腔 14的超声发射单元 1的数目可以是一个， 也可以是单层多个超声发射单元， 也可以是多层多个超声发射单元。所述一个 或多个超声发射单元采用具有反射超声波功能的自聚焦超声换能器单元。 其 中， 图 8中所示的 Z轴方向为该球台形腔 14的声轴线方向， Z轴与该球台形腔 14的中心轴线重合。
当该球台形腔 14由多个超声发射单元拼合形成时， 所述多个超声发射单 元所发射的超声波的频率相同。所述超声发射单元所发射的超声波的波阵面为 半径相同的球面。
本实施例中的超声换能器适合于对子宫肌瘤等疾病进行治疗。当对子宫肌 瘤等疾病进行治疗时， 为了适应独特的体位治疗， 可以采用本实施例中这种不 规则球台形球面共振腔的超声换能器。
实施例 5 :
本实施例与实施例 3 的区别在于， 超声换能器中的超声发射单元是由发 射平面超声波的压电材料以及聚焦透镜组合形成， 即超声发射单元采用透镜聚 焦超声换能器单元。 如图 9、 10、 11所示， 本实施例中， 球面共振腔由四个平 面压电晶片 15以及四个聚焦透镜 16构成， 即每个平面压电晶片 15上都附着 有一个聚焦透镜 16，该四个透镜聚焦超声换能器单元所发射的超声波也为球面 波， 其所发射的超声波的波阵面也为半径相同的球面。
由于上述四个聚焦透镜 16的内表面都为一部分球面， 各个聚焦透镜到球 心的距离相同， 其共同拼合在一起形成一个包含球心在内的球台形腔（当然也 可以拼合形成球壳形腔或球缺形腔） ， 也就是说， 该超声换能器所形成的球面 共振腔的内腔体形状为一个包含球心的截球壳形， 该截球壳形球面共振腔的内 腔体采用球台形腔。
本实施例中其他的结构以及使用都与实施例 3相同， 这里不再赘述。 可以理解的是， 以上实施方式仅仅是为了说明本发明的原理而采用的示 例性实施方式，然而本发明并不局限于此。对于本领域内的普通技术人员而言， 在不脱离本发明的精神和实质的情况下， 可以做出各种变型和改进， 这些变型 和改进也视为本发明的保护范围。

Claims

权 利 要 求 书
1. 一种超声换能器， 包括一个或多个超声发射单元， 其特征在 于所述一个或多个超声发射单元所发射的超声波的波阵面为半径相 同的球面， 该一个或多个超声发射单元同时具有反射超声的功能， 所 述一个超声发射单元形成一个球面共振腔 /或所述多个超声发射单元 共同构成一个球面共振腔，所述球面共振腔的内腔体的形状为球壳形 或者为包含球心在内的截球壳形，所述一个或多个超声发射单元所发 射的超声波的聚焦区域为所述球面共振腔的球心。
2. 根据权利要求 1所述的超声换能器， 其特征在于球面共振腔 的内腔体的形状为包含球心在内的截球壳形，该截球壳形的内腔体采 用球缺截球壳形内腔体或球台截球壳形内腔体。
3. 根据权利要求 2所述的超声换能器， 其特征在于所述球面共 振腔的内腔体的形状为包含球心在内的球台截球壳形，该球台截球壳 形内腔体的上底面 （S 1 ) 与下底面 （S2 ) 平行， 且上底面到球心的距 离与下底面到球心的距离相等；或者所述球面共振腔内腔体的形状为 包含球心在内的球台截球壳形，该球台截球壳形内腔体的上底面（S 1 ) 与下底面（S2 )平行， 且上底面到球心的距离与下底面到球心的距离 不相等。
4. 根据权利要求 2所述的超声换能器， 其特征在于所述球面共 振腔的内腔体的形状为包含球心在内的球台截球壳形，该球台截球壳 形内腔体的上底面 （S 1 ) 与下底面 （S2 ) 不平行， 其上底面到球心的 距离与下底面到球心的距离相等或不相等。
5. 根据权利要求 2所述的超声换能器， 其特征在于所述球缺截 球壳形内腔体的形状包括一个球冠形腔和一个包含有球心在内的球 台形腔， 所述球冠形腔的底面与所述球台形腔的一个底面相吻合， 且 连接在一起，所述球冠形腔和球台形腔之间的连接为可拆卸式连接或 固定连接。
6. 根据权利要求 1所述的超声换能器， 其特征在于所述球面共 振腔的内腔体的形状为球壳形，所述球壳形内腔体的形状包括一个球 缺形腔和一个球冠形腔，所述球缺形腔的底面与球冠形腔的底面相吻 合， 且连接在一起， 所述球缺形腔和球冠形腔之间的连接为可拆卸式 连接或固定连接；或者所述球壳形内腔体的形状包括一个包含有球心 在内的球台形腔和分设于所述球台形腔上、下端的两个球冠形腔， 所 述两个球冠形腔的底面分别与球台形腔的上底面和下底面相吻合，且 两两连接在一起，所述球台形腔与两个球冠形腔之间的连接为可拆卸 式连接或固定连接。
7. 根据权利要求 1-6之一所述的超声换能器， 其特征在于所述 超声发射单元采用多个，所述多个超声发射单元所发射的超声波的频 率相同。
8.根据权利要求 7 所述的超声换能器， 其特征在于所述多个超 声发射单元的工作频率范围为 20KHz— 10MHz。
9.根据权利要求 8 所述的超声换能器， 其特征在于所述多个超 声发射单元的工作频率为 0. 1MHz— 0. 6MHz。
10.根据权利要求 7所述的超声换能器， 其特征在于所述球面共 振腔上开有可供图像监控设备通过的孔 （20 ) 。
11. 根据权利要求 7 所述的超声换能器， 其特征在于所述多个 超声发射单元采用自聚焦超声换能器单元或透镜聚焦超声换能器单 元。
12.根据权利要求 1-6之一所述的超声换能器， 其特征在于所述 一个或多个超声发射单元的工作频率范围为 20KHz— 10腿2。
13.根据权利要求 12 所述的超声换能器， 其特征在于所述一个 或多个超声发射单元的工作频率为 0. 1MHz— 0. 6MHz。
14. 根据权利要求 1一 6之一所述的超声换能器， 其特征在于所 述球面共振腔上开有可供图像监控设备通过的孔 （20 ) 。
15. 根据权利要求 1一 6之一所述的超声换能器， 其特征在于所 述一个或多个超声发射单元采用自聚焦超声换能器单元或透镜聚焦 超声换能器单元。
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